JP7052989B2 - Respiratory assist device, respiratory assist method - Google Patents

Description

The present invention relates to a respiratory assist device, such as a ventilator.

Automatic ventilators designed to regulate or assist ventilation by connecting to the airways of the user (patient) are widely used in the medical field and are commonly referred to as ventilators. For example, a device (respiratory assist device) designed to assist a patient's inspiration in synchronization with the patient's inspiratory effort is a type of ventilator. Among the respiratory assist devices, sleep apnea syndrome (SAS) is a disease that has been increasingly applied in recent years. SAS occurs when the muscles of the airways relax during sleep, lowering the base of the tongue and soft palate, and obstructing the airways. The number of potential SAS patients in Japan is said to be more than 3 million. The risk of developing cardiovascular disease in SAS patients is thought to be 2 to 4 times higher than in healthy individuals, and SAS patients are more likely to have sleep disorders with severe sleep apnea, resulting in traffic accidents. The risk is more than double that of a healthy person. For this type of patient, continuous positive airway pressure (CPAP: Continuous Positive Airway Pressure) using a respiratory assist device (see Patent Document 1) equipped with a blower that applies positive pressure (positive pressure) to the airways. Pressure) is valid. Such breathing aids deliver compressed air supplied by the blower to the patient's airways.

FIG. 11 shows a configuration diagram of a conventional respiratory assist device (CPAP) 301. The user 400 wears a breathing interface device 410 such as a nasal mask that covers the nose. The respiratory interface device 410 is fixed to the head by a fixative, and positive pressure is continuously applied to the airway even during sleep to prevent obstruction of the airway. The conventional breathing assist device 301 is provided with a blower (blower) 340, a humidifying device 350, and the like, and gas is provided from the breathing interface device 410 to the airway of the user 400 through the breathing circuit 370. The gas is moistened from the humidifying device 350, warmed by the heating unit 380 to prevent dew condensation, and then sent to the nose of the user 400. The basic structure of a general ventilator is the same, and how to control the temperature and humidity of the gas to be sent is an extremely important issue.

JP-A-2015-142646

Terumo Corporation, [online], [Search on September 7, 2016], Internet (URL: http://www.terumo-taion.jp/health/sleep/01.html)

However, the respiratory assist device used for respiratory assist has been developed with a focus on the function of relieving airway obstruction, and much attention has not been paid to improving the comfort during use. rice field.

For example, the gas delivered by a respiratory assist device that assists breathing for CPAP is generally provided at a constant temperature and humidity, that is, the temperature of the gas is 37 ° C. and the humidity is 100% relative humidity. This follows the temperature and humidity of the gas sent from the ventilator during tracheal intubation, and the comfort of the user has not been fully investigated.

FIG. 12 is a graph schematically showing the research results by Uchiyama et al., Which is cited as Non-Patent Document 1. Shown in region 510 is a graph showing the relationship between time and core body temperature. Shown in region 520 is a graph showing the relationship between time and the relative temperature of the instep of the limbs to the body. Shown in region 530 is a graph showing the relationship between time and sleepability, and the larger the value on the vertical axis, the easier it is to sleep. Comparing the region 510 and the region 530, it can be seen that when the internal temperature of the body (deep body temperature) is low, the sleepability becomes stronger. It can be seen that during sleep, the core body temperature is lower than during awakening, and in particular, when the core body temperature indicated by L1 to L3 is low, the ease of sleep (see region 530) peaks. The human lungs are thought to play a role like a radiator that releases heat inside the body to the external environment through breathing. Sending hot gas into the airways during sleep is nothing more than blocking it when the body is trying to lower its temperature. Therefore, conventional breathing aids are likely to prevent the user from getting a good night's sleep. Approximately half of the people who use breathing aids for breathing assistance stop using them within a year of starting use, in addition to the noise and inconvenience of the equipment. Difficulty in getting sleep is also considered to be the cause.

In view of such circumstances, the present invention is intended to provide a respiratory assisting device capable of comfortably providing respiratory assist even during sleep.

(1) The present invention includes a breathing interface device that is attached to a user and delivers gas, a gas temperature measuring unit that measures the gas temperature, which is the temperature of the gas, and a heating unit that heats the gas. A temperature fluctuating unit that fluctuates the gas temperature by controlling the heating unit and a biometric information acquisition unit that acquires the biometric information of the user, and the temperature fluctuating unit is based on the biometric information. Provided is a breathing assist device characterized in that the heating unit is controlled so as to fluctuate the gas temperature.

According to the invention described in (1) above, the biometric information acquisition unit for acquiring the biometric information of the user is provided, and the temperature of the gas to be sent can be changed based on the acquired information, so that the user can use the invention. It is possible to send gas at the optimum temperature, which has the excellent effect of improving user comfort.

(2) The present invention further includes a sleep level determination unit that determines a sleep level indicating the sleep level of the user based on the biological information acquired by the biological information acquisition unit, and the temperature fluctuation unit includes the temperature fluctuation unit. The respiratory assist device according to (1) above, wherein the heating unit is controlled so as to fluctuate the gas temperature based on the sleep level.

According to the invention described in (2) above, since the sleep level determination unit for determining the sleep level of the user based on the biological information acquired by the biological information acquisition unit is provided, the temperature suitable for the sleep level of the user is provided. The temperature of the air supply gas can be changed, which has an excellent effect of improving the comfort of the user.

(3) The present invention provides the respiratory assist device according to the above (1) or (2), wherein the biological information acquisition unit has an electroencephalogram measuring unit for measuring an electroencephalogram of the user. ..

According to the invention described in (3) above, since the biological information acquisition unit includes an electroencephalogram measuring unit that measures the user's electroencephalogram, the temperature of the gas to be supplied fluctuates based on the measured electroencephalogram of the user. It is possible to make it. Therefore, it has an excellent effect of improving the comfort of the user.

(4) The present invention includes a state determination unit for determining whether the user is in an awake state or a sleeping state based on the electroencephalogram measured by the electroencephalogram measuring unit. The respiratory assist device according to (3) above is provided.

Generally, when a person goes to sleep, the core body temperature of a person drops. Therefore, for example, if a gas having a temperature higher than the body surface temperature is continuously supplied, the decrease in the core body temperature is hindered, which is unpleasant for the user and may deteriorate the quality of sleep in some cases. According to the invention described in (4) above, since the state determination unit for determining whether the user is in the awake state or the sleep state based on the brain wave is provided, if the user is in the sleep state. , The temperature of the gas to be sent can be changed to a temperature suitable for sleeping, which has an excellent effect of improving the comfort of the user.

(5) The present invention is characterized by comprising a brain wave determination unit for determining whether the user is in a REM sleep state or a non-REM sleep state based on the brain wave measured by the brain wave measurement unit. The respiratory assist device according to the above (3) or (4) is provided.

Human sleep is classified into REM sleep and non-REM sleep according to the way the brain works. In general, sleep alternates between non-REM sleep and REM sleep, from falling asleep to waking up. And there is a correlation between the repeated process and the time change of core body temperature. According to the invention described in (5) above, since non-REM sleep and REM sleep can be determined from the measured brain waves, the state of core body temperature can be estimated, and the temperature of the insufflation gas is set to a temperature suitable for the user. It has the excellent effect of being variable.

(6) In the present invention, the temperature fluctuation unit controls the heating unit to raise the gas temperature or raise the gas temperature based on whether the user is in the REM sleep state or the non-REM sleep state. The respiratory assist device according to (5) above, which is characterized by lowering, is provided.

It is known that the core body temperature of a person decreases with the transition from the first REM sleep to the non-REM sleep after falling asleep, and the core body temperature increases as the stage of the non-REM sleep becomes shallower. .. According to the invention described in (6) above, since the change in the core body temperature can be estimated based on the brain wave, the temperature of the gas to be sent can be changed so as not to interfere with the natural fluctuation of the core body temperature. It has the excellent effect of improving the comfort of the body.

(7) In the present invention, when the brain wave determination unit determines that the user is in the non-rem sleep state, the temperature fluctuation unit controls the heating unit to lower the gas temperature. (5) or the respiratory assist device according to the above (6). In general, sleep alternates between non-REM sleep and REM sleep, from falling asleep to waking up. And there is a correlation between the repeated process and the time change of core body temperature. Specifically, it is known that the core body temperature tends to decrease as the sleep stage of non-rem sleep becomes deeper, and the core body temperature decreases with each non-rem sleep repeated several times until waking up. According to the invention described in (7) above, when it is determined to be in a non-rem sleep state, the temperature fluctuation part controls the heating part to lower the gas temperature, which hinders the natural change of the core body temperature. It has the excellent effect of being able to change the temperature of the gas so that it does not occur.

(8) In the present invention, the brain wave determination unit determines the degree of the non-rem sleep of the user, and the temperature fluctuation unit controls the heating unit based on the degree of the non-rem sleep. The respiratory assist device according to any one of the above (5) to (7), which is characterized by raising or lowering the gas temperature.

A person's core body temperature tends to decrease when the degree of non-rem sleep, specifically the sleep stage of non-rem sleep, becomes deeper and is maintained when the degree of non-rem sleep becomes shallower. According to the invention described in (8) above, since the electroencephalogram determining unit capable of determining the degree of non-rem sleep is provided, the temperature of the gas can be changed so as not to interfere with the natural change in the core body temperature. It has an excellent effect.

(9) The present invention includes a breathing interface device that is attached to the user and delivers gas, a gas temperature measuring unit that measures the gas temperature, which is the temperature of the gas, and a heating unit that heats the gas. The breathing unit includes a temperature fluctuation unit that fluctuates the gas temperature by controlling the heating unit, and the temperature fluctuation unit further includes a timer processing unit that controls the gas temperature with the passage of time. Provide auxiliary equipment.

According to the invention described in (9) above, since the temperature fluctuation unit has a timer processing unit that controls the gas temperature according to the passage of time, the gas temperature can be controlled easily according to a preset timer program. It has the effect of improving user comfort.

(10) In the present invention, the timer processing unit maintains the temperature of the gas at a temperature equal to or higher than the body surface temperature of the user for a predetermined time after the user starts operating the device. The respiratory assist device according to (9) above, which is characterized by performing control, is provided.

When insufflating gas through the nasal cavity, the gas temperature slightly higher than the body surface temperature may improve the passage of the nasal cavity in the awake state. According to the invention described in (10) above, the temperature of the insufflation gas is set to the body surface temperature for an average time, for example, 30 minutes, which is considered to take from the time when the user starts operating the device to when he / she falls asleep. Maintaining the above temperature has an excellent effect of improving the passage of the nasal cavity and making it easier for the user to fall asleep.

(11) The present invention provides the respiratory assist device according to the above (9) or (10), wherein the timer processing unit stops the heating unit.

Generally, the transition from wakefulness to sleep lowers a person's core body temperature. Therefore, for example, if a gas having a temperature higher than the body surface temperature is continuously supplied, the decrease in the core body temperature is hindered, which is unpleasant for the user and may deteriorate the quality of sleep in some cases. According to the invention described in (11) above, the heating of the gas is automatically stopped after an average time, for example, 30 minutes, which is considered to take from the time when the user starts operating the device until the user falls asleep. Therefore, the temperature of the gas can be lowered to at least room temperature so as not to interfere with the natural change in the core body temperature, which has an excellent effect of improving the comfort of the user.

(12) The present invention is characterized in that the timer processing unit controls the temperature of the gas to be equal to or lower than the body surface temperature of the user according to the above (9) or (10). The described respiratory assist device is provided.

Generally, the transition from wakefulness to sleep lowers a person's core body temperature. Therefore, for example, if a gas having a temperature higher than the body surface temperature is continuously supplied, the decrease in the core body temperature is hindered, which is unpleasant for the user and may deteriorate the quality of sleep in some cases. According to the invention described in (12) above, the temperature of the gas to be sent can be automatically lowered from the body surface temperature over time, so that the temperature of the gas does not interfere with the natural change in the core body temperature. The temperature can be lowered to at least room temperature, which has an excellent effect of improving the comfort of the user.

(13) The present invention is characterized in that the timer processing unit controls the temperature of the gas to be higher than the melting point of water in the environment in which the apparatus is operated. The described respiratory assist device is provided.

The device is intended for users who have few problems except for the respiratory organs, and lowering the temperature of the insufflation gas more than necessary rather impairs the user's comfort. According to the invention described in (13) above, it is unnecessary to maintain the temperature of the air supply gas at a temperature higher than the freezing point of water, specifically the melting point of water in the environment in which the device is operated. Since it prevents cold gas from being sent in, it has an excellent effect that it does not impair the comfort of the user.

(14) In the present invention, the timer processing unit has an ascending region for raising the temperature of the gas, a descending region for lowering the temperature of the gas, and the gas according to a predetermined order and time interval input in advance. The respiratory assist device according to any one of the above (9) to (13) is provided, wherein the control is performed so as to include a maintenance region for keeping the temperature at a constant temperature.

A person's core body temperature fluctuates over time from falling asleep to waking up. According to the invention described in (14) above, the temperature of the gas to be supplied can be changed according to a predetermined order and time interval input in advance, so that the temperature of the gas to be supplied can be changed according to the expected time fluctuation of the core body temperature. It has the excellent effect of being able to supply air at the optimum gas temperature and improving the comfort of the user.

(15) The present invention is a method for controlling a breathing assist device that delivers gas to a sleeping user, wherein the breathing assist device measures a gas temperature, which is the temperature of the gas, and a gas temperature measuring step. A heating step in which the breathing assist device heats the gas, a temperature fluctuation step in which the breathing assist device fluctuates the gas temperature by controlling a heating unit, and the breathing assist device is used. A biological information acquisition step for acquiring a person's biological information is provided, and the temperature fluctuation step by the respiratory assist device changes the gas temperature by changing the heating step based on the biological information during sleep. Provided is a control method of a respiratory assist device, which is characterized in that the control is performed so as to cause the breathing.

According to the invention of the method described in (15) above, the biometric information acquisition step for acquiring the biometric information of the user is provided, and the temperature of the gas to be sent can be changed based on the acquired information. It is possible to send gas at the optimum temperature for the user, and it has an excellent effect of improving the comfort of the user.

(16) The present invention is a method for controlling a breathing assist device that delivers gas to a sleeping user, wherein the breathing assist device measures a gas temperature, which is the temperature of the gas, and a gas temperature measuring step. The breathing assist device comprises a heating step for heating the gas and a temperature fluctuation step in which the breathing assist device changes the gas temperature by controlling a heating unit, and the breathing assist device is used. The temperature fluctuation step provides a control method for a breathing assist device, further comprising a timer processing step that modifies the heating step to control the gas temperature over time.

According to the invention of the method described in (16) above, since the temperature fluctuation step has a timer processing step for controlling the gas temperature with the passage of time, the gas temperature can be controlled according to a preset timer program. It easily has the effect of improving user comfort.

The present invention includes a breathing interface device that is attached to the user and delivers gas, a gas temperature measuring unit that measures the gas temperature, which is the temperature of the gas, a heating unit that heats the gas, and the above. A breathing assist device may be provided that includes a temperature fluctuating section that fluctuates the gas temperature by controlling the heating section.

According to the above invention, since it has a temperature fluctuating part that fluctuates the gas temperature, in respiratory assistance, the gas temperature is not simply sent to a constant temperature, but to the optimum temperature for the user at any given time. Can be varied. Therefore, according to the present invention, it has an excellent effect of improving the comfort of the user.

The present invention is characterized in that, when a predetermined time elapses from the start of operation of the breathing assist device, the temperature fluctuating section controls the heating section to lower the gas temperature. May be provided.

When assisting breathing, it is more comfortable for the user to send warm gas before and after the start of sleep, and it often improves the passage of the nasal cavity. However, since the core body temperature drops when falling asleep, it is desirable to lower the temperature of the insufflation gas as well. According to the above invention, the gas is maintained at a constant temperature for a predetermined time from the start of operation of the respiratory assist device to improve the ventilation of the nasal cavity, and then the gas temperature is lowered by controlling the heating part. It has an excellent effect of not hindering the decrease in core body temperature during sleep in the user.

The present invention may further provide a breathing assist device comprising a humidifying device for humidifying the gas.

According to the above invention, since the respiratory assist device further includes a humidifying device for humidifying the gas, it has an excellent effect that the respiratory assist can be performed without excessively drying the airway and the nasal cavity.

The present invention provides a breathing assist device, wherein the humidifying device includes a water storage section for storing water for humidification and a porous hollow fiber section to which water is supplied from the water storage section. You may.

The humidifying device provided in the conventional respiratory assist device boils and evaporates water by heating with a heater to generate water vapor. Therefore, there is a problem that it is difficult to freely control the temperature of the gas to be sent. According to the above humidifying device, the hollow fiber can suck up water from the water storage part by the capillary phenomenon, and since the surface of the hollow fiber is porous, the water evaporates through the fine pores to supply air. The gas can be humidified. By providing such a humidifying device in the respiratory assist device, humidification without heating by a heater becomes possible, so that the gas temperature can be easily controlled, which is an excellent effect.

The present invention is characterized by comprising a gas humidity measuring unit that measures the gas humidity, which is the humidity of the gas, and a humidity fluctuation unit that controls the humidifying device to change the gas humidity to a predetermined humidity. A breathing aid may be provided.

According to the above invention, since the breathing assist device includes a gas humidity measuring unit for measuring the humidity of the gas and a humidity fluctuation unit for varying the gas humidity to a predetermined humidity, the gas having the optimum humidity for the user is supplied. It has a remarkably excellent effect of being able to do it.

The present invention provides the above-mentioned respiratory assist device, wherein the humidity fluctuation unit controls the humidifying device so that the amount of water vapor supplied becomes a predetermined amount from the correlation between the gas humidity and the gas temperature. May be good.

The amount of water vapor that can be contained in the air is determined by the temperature. Therefore, the optimum amount of water vapor for the user changes depending on the temperature of the gas sent by the respiratory assist device. According to the above invention, the humidity fluctuation unit can control the humidifying device so that the amount of water vapor supplied becomes a predetermined amount from the correlation between the gas humidity and the gas temperature, so that the excellent effect of improving the comfort of the user can be obtained. Play.

The present invention may provide a breathing assist device characterized in that the humidity fluctuation unit has a timer processing unit that controls the gas humidity with the passage of time.

According to the above invention, since the humidity fluctuation unit has a timer processing unit that controls the gas humidity according to the passage of time, the gas humidity can be controlled according to a preset timer program, and the user's comfort can be easily obtained. It has the effect of improving.

The present invention may provide a breathing assist device characterized in that the temperature fluctuation unit has a timer processing unit that controls the gas temperature with the passage of time.

According to the above invention, since the temperature fluctuation unit has a timer processing unit that controls the gas temperature according to the passage of time, the gas temperature can be controlled according to a preset timer program, and the user's comfort can be easily achieved. It has the effect of improving.

The present invention includes a biometric information acquisition unit that acquires biometric information of the user, and the humidity fluctuation unit controls the humidifying device so as to fluctuate the gas humidity based on the biometric information. A breathing assist device comprising the above may be provided.

According to the above invention, it is possible to send a gas having an optimum humidity for the user based on the biometric information acquired by the biometric information acquisition unit, so that an excellent effect of improving the comfort of the user can be achieved. Play.

The present invention includes a biometric information acquisition unit that acquires biometric information of the user, and the temperature fluctuating unit controls the heating unit so as to fluctuate the gas temperature based on the biometric information. A respiratory assist device characterized by this may be provided.

According to the above invention, the biometric information acquisition unit for acquiring the biometric information of the user is further provided, and the temperature of the gas to be sent can be changed based on the acquired information, so that the optimum temperature for the user can be changed. It is possible to send the gas of the air, and it has an excellent effect of improving the comfort of the user.

The present invention may provide a breathing assist device characterized in that the biological information acquisition unit has a deep body temperature measuring unit that measures the deep body temperature, which is the temperature of the deep body of the user.

According to the above invention, since it is possible to measure the core body temperature, which is the temperature of the deep part of the living body of the user, it is possible to measure the core body temperature during sleep and change the temperature of the gas according to the change. It has an excellent effect.

The present invention is characterized in that the temperature fluctuation unit controls the heating unit so as to decrease the gas temperature when the core body temperature measured by the core body temperature measuring unit decreases. Breathing aids may be provided.

In general, it is known that the core body temperature decreases during sleep, and there is a research result that promoting the decrease in the core body temperature makes it easier to fall asleep. According to the above invention, when the core body temperature measured by the core body temperature measuring unit decreases, the heating unit can be controlled so as to decrease the temperature of the gas to be supplied, so that when performing respiratory assistance. It does not interfere with sleep and has an excellent effect of improving user comfort.

The present invention may provide a respiratory assist device characterized in that the temperature fluctuation unit controls the gas temperature to be equal to or lower than the core body temperature.

According to the above invention, since the temperature of the gas sent by the respiratory assist device can be controlled to be lower than the core body temperature, it is possible to promote the decrease of the core body temperature by the gas, which is excellent in facilitating falling asleep. Has an effect.

The present invention also provides the above-mentioned respiratory assist device, wherein the biological information acquisition unit has a body surface temperature measuring unit that measures a body surface temperature, which is the temperature of the body surface of the user. good.

It is known that in humans, the core body temperature decreases and at the same time, the body surface temperature, which is the temperature of the body surface, rises conversely. It is believed that this is because heat is released from the body surface in order to lower the core body temperature. According to the above invention, by providing a means for measuring the body surface temperature and reflecting the measurement result on the temperature of the gas to be sent, it is possible to improve the comfort of the user and the sleeping state. It works.

The present invention is characterized in that the temperature fluctuation unit controls the heating unit so as to lower the gas temperature when the body surface temperature measured by the body surface temperature measuring unit rises. A breathing assist device may be provided.

As described above, it is known that during sleep, the core body temperature decreases and at the same time, the body surface temperature, which is the temperature of the body surface, rises conversely. According to the above invention, when the body surface temperature of the user measured by the body surface temperature measuring unit rises, the temperature fluctuating unit controls the heating unit so as to lower the gas temperature. It has an excellent effect of being able to realize a comfortable breathing assist device with a high therapeutic effect for the person.

The present invention further includes an outside air temperature measuring unit that measures the outside air temperature, which is the temperature of the place where the user is, and the temperature fluctuating unit controls the gas temperature based on the outside air temperature. A breathing assist device comprising the above may be provided.

It is considered that humans control their metabolic activities and others so that they have the best sleeping environment when they breathe at the temperature (outside air temperature) of the place where they are sleeping during sleep. In the conventional respiratory assist that sends the gas heated by the heater heating type humidifier attached to the respiratory assist device to the airway, it means that you are sleeping while taking in excess heat energy, and you sleep. May have an adverse effect on. According to the above invention, the outside air temperature measuring unit for measuring the outside air temperature is provided, and the temperature fluctuating unit determines the temperature of the gas to be sent based on the outside air temperature. It has an excellent effect of being able to do it.

In the present invention, when the outside air temperature is defined as Tout (the unit is Celsius temperature: ° C.), the temperature fluctuation unit sets the gas temperature between (Tout-1) ° C. and (Tout-3) ° C. Respiratory assist devices characterized by control may be provided.

Injecting excessively cold gas into the nasal passages can cause nasal congestion. According to the above invention, the temperature fluctuation unit controls the temperature of the gas to be supplied between (Tout-1) ° C. and (Tout-3) ° C., so that the gas having a moderately low temperature is supplied. This makes it possible to improve the comfort of the user and achieve both the effects of treatment.

The present invention may provide a respiratory assist device characterized in that the biological information acquisition unit has a body movement measuring unit for measuring the body movement of the user.

Human sleep states are broadly divided into deep sleep "Non-REM sleep (Non-REM sleep)" state and light sleep "REM sleep (Rapid eye Movement sleep)" state. .. It is known that the body movement decreases in the "non-REM sleep" state and increases in the "REM sleep" state. By detecting the body movement with an accelerometer or the like, a human can be in either sleep state. You can tell if there is one. According to the above invention, the breathing assist device can measure the body movement by the body movement measuring unit and send the gas having the temperature and humidity according to each sleeping state, so that the breathing assistance is comfortable for the user. It has the excellent effect of being able to realize the device.

The present invention includes a sleep depth determination unit that determines the sleep depth of the user from the body movement measured by the body movement measurement unit, and lowers the gas temperature when the sleep depth deepens. A breathing assist device characterized by having the patient may be provided.

In the so-called "non-rem sleep" state of deep sleep, humans have a decrease in core body temperature and slow breathing. According to the above invention, the breathing assist device includes a sleep depth determination unit that determines the sleep depth of the user from the body movement, and the core body temperature is generated when shifting to the “non-rem sleep” state, which is a deep sleep. Since it is possible to lower the temperature of the gas in the same way as lowering the temperature of the gas, it has an excellent effect of realizing a breathing assist device that is comfortable for the user.

The present invention is a method for controlling a breathing assist device that delivers gas to a sleeping user, in which a gas temperature measuring step for measuring the gas temperature, which is the temperature of the gas, and heating for heating the gas are provided. A breathing assisting method may be provided comprising a step and a temperature fluctuation step in which the gas temperature is fluctuated during sleep by controlling the heating unit.

According to the invention of the above method, since it has a temperature fluctuation step that fluctuates the gas temperature, in respiratory assistance, instead of simply insufflating gas at a constant temperature, the optimum temperature for the user at any given time is obtained. The gas temperature can be changed. Therefore, according to the method of the present invention, an excellent effect of improving the comfort of the user is obtained.

According to the present invention, the biometric information acquisition unit for acquiring the biometric information of the user is provided, and the temperature of the gas to be sent can be changed based on the acquired information, so that the gas having the optimum temperature for the user can be obtained. It is possible to supply air and has an excellent effect of improving user comfort.

Further, according to the present invention, since the temperature fluctuation unit has a timer processing unit that controls the gas temperature according to the passage of time, the gas temperature can be controlled according to a preset timer program, and the user's comfort can be easily achieved. It has the effect of improving.

It is explanatory drawing of the respiratory assist device which concerns on 1st Embodiment of this invention. It is a block diagram of the control device which controls a breathing assist device. It is a flowchart about the temperature control of the gas to send air. It is a graph which shows the example of a gas temperature control. It is explanatory drawing of the respiratory assist device which concerns on 2nd Embodiment of this invention. It is a block diagram of the control device which controls a breathing assist device. It is a flowchart about temperature control and humidity control of a gas to send air. It is explanatory drawing of the respiratory assist device which concerns on 3rd Embodiment of this invention. (A) It is a block diagram of the control device which controls a respiratory assist device. (B) It is a graph which shows the example of a gas temperature control. It is a block diagram of the control device which concerns on a modification. It is sectional drawing of the humidifying apparatus which concerns on a modification. It is explanatory drawing of the conventional respiratory assist device. It is a graph showing the relationship between the time and the core body temperature (region 510), the time and the relative temperature of the instep of the limbs to the body (region 520), and the time and sleepability (region 530), respectively. It is explanatory drawing of the respiratory assist device which concerns on 4th Embodiment of this invention. It is a block diagram of the control device which controls a breathing assist device. It is explanatory drawing about the correlation of the sleep depth and the core body temperature. It is a flowchart about the control which fluctuates the temperature of an air supply gas based on an electroencephalogram. (A) It is a block diagram of the control device which controls the respiratory assist device which concerns on 5th Embodiment of this invention. (B) It is a graph which shows the control result which changed the air supply gas temperature according to the predetermined order and time interval.

Hereinafter, embodiments of the present invention will be described with reference to the accompanying drawings. 1 to 17 are examples of embodiments in which the invention is carried out, and in the drawings, portions with the same reference numerals represent the same objects. It should be noted that some configurations are appropriately omitted in each drawing to simplify the drawings. Then, the size, shape, thickness, etc. of the member are appropriately exaggerated and expressed.

FIG. 1 is an explanatory diagram illustrating a respiratory assist device 1 according to the first embodiment of the present invention. The breathing assist device 1 includes a main body 5, a humidifying device 50 for humidifying the gas to be supplied, a breathing circuit 70 including a conduit for transporting the gas to be supplied, and heating for heating the gas in the breathing circuit. The unit 80 includes a breathing interface device 110 that is attached to the user and delivers gas, and a deep body temperature measuring sensor 120 that detects the deep body temperature, which is the temperature of the deep part of the living body of the user. The respiratory interface device 110 is preferably a nasal mask and a nasal prong. In order to prevent the pressure from increasing due to exhalation and making it difficult to exhale, it is desirable that a so-called relief valve, which opens to the atmosphere when the pressure increases, is provided in or near the breathing interface device 110.

The main body 5 has a blower (blower) 40 for supplying compressed gas, a flow rate measuring device 20 for measuring the flow rate of the supplied gas, and a control device 10 for controlling the flow rate, pressure, and temperature of the gas. The blower (blower) 40 sucks in outside air from the intake port 30, compresses it, and sends it out to the breathing circuit 70. At this time, the flow rate of the gas to be sent is measured by the flow rate measuring device 20, and the control device 10 controls the prescription pressure prescribed by the doctor. It is desirable to have a pressure gauge that measures the pressure of the gas to be sent.

A breathing interface device 110 is connected to the breathing circuit 70, and positive pressure gas is applied from the breathing interface device 110 to the nasal cavity of the user 100. The breathing circuit 70 or the breathing interface device 110 is provided with a gas temperature sensor 105 that detects the gas temperature, which is the temperature of the gas in the vicinity of the breathing interface device 110. Further, a heating unit 80 is provided in at least a part of the breathing circuit 70, and the gas temperature is controlled by controlling the heater power supply 90 by the control device 10.

The humidifying device 50 is connected to the main body 5 or the breathing circuit 70 and humidifies the gas sent to the user. The humidifying device 50 includes a water storage unit 55 for storing water for humidification and a porous hollow fiber unit 60 to which water from the water storage unit is supplied. The porous hollow fiber portion 60 is inserted into the breathing circuit 70, and humidifies the gas in the breathing circuit 70 by evaporating water vapor.

The core body temperature measurement sensor 120 may be a heat flow compensation type or a method including a plurality of heat flow sensors.

FIG. 2 shows a configuration diagram of the control device 10. The control device 10 includes a biometric information acquisition unit 140 that acquires biometric information of the user, a temperature fluctuation unit 130 that fluctuates the gas temperature by controlling the heating unit 80, and a gas temperature measurement unit 180 that measures the gas temperature. Has. The biological information acquisition unit 140 has a deep body temperature measuring unit 160 that measures the core body temperature (see FIG. 1). The temperature fluctuation unit 130 is connected to the heater power supply 90, and the deep body temperature measuring unit 160 is connected to the deep body temperature measuring sensor 120 (see FIG. 1). As will be described later, the temperature fluctuation unit 130 controls the temperature of the heating unit 80 so as to fluctuate the gas temperature based on the core body temperature which is the biological information. The gas temperature measuring unit 180 is connected to the gas temperature sensor 105 and measures the temperature of the gas (see FIG. 1). At this time, it is desirable that the control device 10 performs feedback control (for example, PID control) of the heating unit 80 based on the temperature of the gas obtained by the gas temperature measuring unit 180.

The control device 10 is composed of a CPU, RAM, ROM, and the like, and executes various controls. The CPU is a so-called central processing unit, and various programs are executed to realize various functions. The RAM is used as a work area and a storage area of the CPU, and the ROM stores an operating system or a program executed by the CPU.

FIG. 3A shows a flowchart of the temperature control of the gas temperature performed by the control device 10.

First, when the power of the respiratory assist device 1 is turned on, the blower (blower) 40 starts operation and starts respiratory assist (see FIG. 1). Although not shown in particular, the set value (prescription pressure, etc.) immediately before the power was turned off last time is automatically reflected when the power is turned on.

A timer function (not shown) for measuring the operation time is activated from the start of the operation, and the gas temperature is maintained at a predetermined temperature, for example, 37 ° C. for a predetermined time, for example, 30 minutes (step S1-10). This is because it is more comfortable for the user to send a relatively warm gas when falling asleep because the passage through the nasal cavity is improved. It is desirable that the predetermined time and the predetermined temperature can be appropriately changed by the user.

When the user goes to sleep after a predetermined time has elapsed from the start of operation of the breathing assist device 1, the core body temperature of the user, which is detected by the core body temperature measurement sensor 120 and measured by the core body temperature measurement unit 160, decreases. start. Along with this, the temperature fluctuation unit 130 of the control device 10 controls the heater power supply 90 to lower the temperature of the heating unit 80, thereby lowering the gas temperature to a predetermined target temperature (step S1-20). This target temperature is lower than the core body temperature, preferably the same as the outside air temperature, or 1 ° C. to 3 ° C. below the outside air temperature. When the target temperature is substantially equal to the outside air temperature, the temperature fluctuation unit 130 may reduce the power given to the heater power supply 90 or set it to zero.

In order to keep the gas temperature lower than the outside air temperature, it is desirable to provide a cooling mechanism. As the cooling mechanism, it may be generally used for gas cooling, and it may be cooled by removing the heat of vaporization from the gas by using a refrigerant and a compressor like a normal refrigerator, or it may be cooled by using a Pelche element. good. It is also conceivable to use the humidifying device 50 itself for cooling.

It is desirable that the target temperature can be changed by the user during operation.

That is, the control device 10 controls the heating unit 80 so as to lower the gas temperature based on the biological information of the core body temperature. In general, the human core body temperature decreases during sleep until just before awakening. Therefore, when the core body temperature measured by the core body temperature measuring unit 160 decreases, the control device 10 heats the gas temperature so as to decrease the gas temperature. It is desirable to control the unit 80. At this time, it is desirable that the control device 10 performs feedback control of the heating unit 80 so as to reach the target temperature by using the gas temperature detected by the gas temperature sensor 105 and measured by the gas temperature measuring unit 180.

After that, the control device 10 maintains the gas temperature at the target temperature and continues the respiratory assistance until the user becomes awake and turns off the power of the respiratory assist device 1 to stop the operation (step S1-30). If NO). When the power of the respiratory assist device 1 is turned off and the operation is stopped, the control of the gas temperature is also stopped at the same time (in the case of YES in step S1-30).

By the above operation, the respiratory assist device 1 can control the heating unit 80 so as to lower the temperature of the gas to be supplied without hindering the lowering of the core body temperature during sleep, so that the respiratory assist device 1 performs respiratory assistance. It does not interfere with sleep and has an excellent effect of improving user comfort. Of course, artificial respiration also improves sleep comfort.

FIG. 3B is a graph showing a modified embodiment of gas temperature control.

FIG. 3B (a) shows an example in which the gas temperature is fluctuated by the temperature fluctuating unit 130 (see FIG. 2) according to a timer (not shown) provided in the respiratory assist device 1 regardless of biological information. The gas temperature is maintained at, for example, 37 ° C. for 30 minutes from the start of operation, which is shown in the period 610, and the gas temperature is lowered by 3 ° C. in the period 620. After that, the gas temperature is maintained at 34 ° C. for 2 hours and 30 minutes (period 630). After that, the gas temperature is further lowered by 3 ° C. (period 640), and the gas temperature is continuously maintained at 31 ° C. for 2 hours (period 650). During the period 660 towards awakening in time, the temperature is raised by 6 ° C and then maintained at 37 ° C (period 670). By operating such a timer, it is possible to easily realize the comfort of the user during sleep.

FIG. 3B (b) shows a case where the core body temperature is measured, the target temperature is lowered in accordance with the drop, and the gas temperature is lowered. In this modified embodiment, the gas temperature is maintained at, for example, 37 ° C. for 30 minutes from the start of operation, then detected by the deep body temperature measuring sensor 120, and in accordance with the decrease in the deep body temperature measured by the deep body temperature measuring unit 160. The gas temperature is being lowered.

Specifically, the core body temperature is measured at predetermined time intervals, and the target temperature is determined at any time according to the measurement (see FIG. 3A). Speaking of FIG. 3B (b), for example, based on a temperature of 34 ° C, which is 2 ° C lower than the average human body temperature of 36 ° C, the time change of the core body temperature is multiplied by a predetermined coefficient, for example, 2.0. The target temperature is changed by the amount of the temperature. That is, the target is to lower the gas temperature by 3 ° C following the decrease in core body temperature by 1.5 ° C during the period 740, and maintain the gas temperature at 31 ° C during the period 750 when the core body temperature does not change. Determine the temperature. In addition, in order to prevent the nasal cavity from being stimulated by sudden fluctuations in gas temperature and disturbing the user's deep sleep, a function in which the temperature change determined by the core body temperature and time is small and the time change is smooth in order to smoothly change the gas temperature. You may decide the target temperature with. Of course, a look-up table of the core body temperature and the target temperature may be prepared in advance in the temperature fluctuation unit 130, and the target temperature may be determined according to the core body temperature measured by the core body temperature measuring unit 160.

In this modified example, the increase in core body temperature, which often occurs during awakening, is not reflected in the gas temperature.

Needless to say, the gas temperature control according to the modified embodiment shown in FIGS. 3B (a) to 3B (b) described above can be applied to other embodiments as well.

FIG. 4 shows an explanatory diagram of the respiratory assist device 1 according to the second embodiment of the present invention. The difference from the first embodiment is a gas humidity sensor 95 that detects the humidity of the gas, and a humidity control unit 65 that adjusts the amount of water vapor supplied from the humidifying device 50 to change the humidity.

As a specific mechanism of the humidity control unit 65 for adjusting the humidity, the amount of water supplied to the porous hollow fiber portion 60 may be adjusted by a solenoid valve, and the heating unit may be attached to the porous hollow fiber portion 60. The amount of water vapor generated may be increased or decreased by providing the above and adjusting the amount of heating thereof.

In the conventional respiratory assist device used for respiratory assist, a gas having a relative humidity of 100% is sent from the airway, and it depends on whether such gas is comfortable for the user. For example, a user who receives CPAP therapy is inflated through the nasal cavity, which can hydrate the gas by itself, and has the ability to humidify on its own. Therefore, in the second embodiment of the present invention, the humidity of the gas to be sent is maintained at a target humidity, for example, a value between 60% and 80% relative humidity, thereby promoting a comfortable sleep for the user. It is desirable that the user can change the target humidity while operating the respiratory assist device 1.

FIG. 5 shows a configuration diagram of the control device 10 in the respiratory assist device 1 according to the second embodiment of the present invention. In addition to the control device 10 of the first embodiment, the control device 10 further includes a humidity fluctuation unit 150 that changes the gas humidity to a predetermined humidity and a gas humidity measurement unit 185 that measures the gas humidity.

That is, the breathing assist device 1 is provided with a gas humidity sensor 95 for detecting the humidity of the gas in the breathing circuit 70, and the control device 10 is provided with a gas humidity measuring unit 185 for measuring the humidity of the gas (FIG. 4). reference). The control device 10 further includes a humidity fluctuation unit 150 that changes the gas humidity to a predetermined humidity, and the humidity fluctuation unit 150 controls the humidity control unit 65. It is desirable that the gas humidity sensor 95 is connected to the gas humidity measuring unit 185, and the humidity fluctuation unit 150 feedback-controls the gas humidity based on the measured gas humidity.

FIG. 6A shows a flowchart of gas temperature and gas humidity control performed by the control device 10. The difference from the first embodiment shown in FIG. 3A is that in (step S2-20), the humidity fluctuation unit 150 of the control device 10 targets the gas temperature as the core body temperature drops after a lapse of a predetermined time. After the operation of lowering the temperature to the temperature, in (step S2-30), the operation of maintaining the gas humidity at a predetermined humidity is performed. This order may be reversed, and (step S2-30) may be performed at the same time as (step S2-10) or before or after (step S2-10).

Although the mode of maintaining the humidity constant has been described here, the humidifying device 50 may be controlled so as to fluctuate the gas humidity based on the biological information in order to improve the comfort of the user. Specifically, the relative humidity may be increased or decreased according to the fluctuation of the core body temperature. For example, when core body temperature drops, you may be sweating more to release heat from your body surface, so set a high target humidity to prevent excessive loss of water from your body. The humidity fluctuation unit 150 may perform control (see FIG. 6 (b)). On the contrary, if the core body temperature rises, the humidity may be lowered.

Further, the humidifying device 50 may be controlled so as to have a predetermined water vapor supply amount from the correlation between the gas humidity and the gas temperature.

FIG. 7 shows an explanatory diagram of the respiratory assist device 1 according to the third embodiment of the present invention. The difference from the second embodiment is the outside air temperature measuring sensor 45 that detects the outside air temperature Tout (unit: Celsius temperature: ° C.), which is the temperature of the place where the user is.

FIG. 8A shows a configuration diagram of the control device 10 in the respiratory assist device 1 according to the third embodiment. The control device 10 further includes an outside air temperature measuring unit 170 connected to the outside air temperature measuring sensor 45 to measure the outside air temperature. The temperature fluctuation unit 130 controls the gas temperature between (Tout-1) ° C. and (Tout-3) ° C. as the target temperature.

In the conventional respiratory assist device used for respiratory assist as described above, the temperature of the supplied gas is maintained at 37 ° C. When falling asleep, the core body temperature drops, and conversely, lowering the core body temperature makes it easier to fall asleep. Therefore, in order for the user to get a more comfortable sleep, the gas temperature of the gas sent from the breathing assist device 1 is the outside air temperature. This is because it is considered preferable that the temperature is the same as or lower than the outside air temperature Tout, for example, by about 1 ° C. to 3 ° C.

FIG. 8B shows a case where the core body temperature is measured, the target temperature is fluctuated according to the fluctuation, and the gas temperature is fluctuated by the temperature fluctuating unit 130 to perform temperature control. In this modified embodiment, the gas is sent at a temperature lower than the outside air temperature. That is, for example, it is assumed that the outside air temperature measured by the outside air temperature measuring unit 170 is constant at 25 ° C. For the first 30 minutes, the gas temperature is maintained at 37 ° C. as in the modified examples above. Subsequently, in the period 820, the gas temperature is lowered in accordance with the decrease in the core body temperature, and in the period 830, the gas temperature is maintained in accordance with the fact that the core body temperature does not fluctuate. After that, during the period 840, the gas temperature was lowered again in accordance with the decrease in the core body temperature, and for the following 1 hour, the gas temperature was maintained at 23 ° C, which was 2 ° C lower than the outside air temperature, as the core body temperature did not fluctuate. (Period 850). In the following period 860, the gas temperature is raised by 2 ° C. as the core body temperature rises, and similarly, the gas temperature is controlled according to the fluctuation of the core body temperature. The gas temperature may be determined in consideration of the fluctuation of the outside air temperature. By controlling the gas temperature in this way, it becomes possible for the user to comfortably assist in breathing.

The cooling mechanism that cools the gas to a temperature lower than the outside temperature may be generally used for gas cooling, and cools the gas by removing the heat of vaporization from the gas using a refrigerant and a compressor like a normal refrigerator. Also, a Pelche element may be used. Of course, it is also conceivable to cool using the humidifying device 50 itself. The gas temperature may be controlled so as to fluctuate according to the change of the core body temperature.

It should be noted that the respiratory assist device according to the present invention is not limited to the above-described embodiment, and it is needless to say that various modifications can be made without departing from the gist of the present invention.

For example, as shown in FIG. 9A, a modified embodiment in which the temperature fluctuation unit 130 included in the respiratory assist device 1 has a timer processing unit 190 can be considered. The timer processing unit 190 controls the gas temperature with the passage of time.

FIG. 9B shows an example in which the gas temperature is changed by the timer processing unit 190. For 30 minutes after starting the operation, the temperature fluctuation unit 130 keeps the gas temperature at 37 ° C., which is slightly higher than the body temperature (period 930). Subsequently, the timer processing unit 190 recognizes that 30 minutes have passed, and lowers the gas temperature to 25 ° C. over 30 minutes with respect to the temperature fluctuation unit 130 (period 940). Then, the timer processing unit 190 recognizes that the period 940 has elapsed, and controls the heating unit 80 so as to maintain the gas temperature at 25 ° C. for the following 1 hour (period 950). Similarly, by operating the timer processing unit 190, the gas temperature is controlled with the passage of time, and the user can comfortably and effectively receive CPAP therapy.

The respiratory assist device 1 has a plurality of operation modes such as a timer mode for controlling the gas temperature according to the passage of time as described above and a biological information mode for changing the gas temperature based on biological information, and a plurality of operations. It may be provided with a selection processing function that allows the user to select one of the modes. In the timer mode, in addition to a plurality of preset sequences, that is, the sequence shown in FIG. 9B, for example, a sequence for lowering the gas temperature at a constant rate over 8 hours is provided and is selected by the user. It may be possible.

Further, for example, in the second embodiment and the third embodiment, a modified embodiment in which the humidity fluctuation unit 150 has the timer processing unit 190 is also conceivable (see FIGS. 5 and 8). The timer processing unit 190 controls the gas humidity with the passage of time.

Further, for example, as the humidifying device, a conventional tank type humidifying device may be used, or a method as shown in FIG. 10 below may be used. FIG. 10 is a cross-sectional view of the humidifying device 210 according to the modified embodiment of the present invention. The humidifying device 210 is connected to the breathing circuit 70 of the respiratory assisting device that regulates or assists ventilation in the user's respiratory organ, similarly to the conventional humidifying device, and moisture is added to the gas to be sent in the form of fine particles or water vapor. give. The humidifying device 210 is arranged between the blower (blower) side pipe 290 and the breathing circuit side pipe 295, and generates at least a liquid container 280 containing a liquid containing water and mist droplets which are minute droplets of the liquid. It has a fog droplet generating means 270 and a water retaining member 220 that holds at least a part of the fog droplets. The mist drop generating means 270 generates mist droplets by ultrasonic vibration in this modified embodiment as described later.

The mist droplet generating means 270 has an ultrasonic wave generating means for generating mist droplets by vibrating a liquid. That is, in the humidifying device according to the present modification, the mist drop generating means 270 is an ultrasonic mist generating means utilizing the so-called cavitation effect in which bubbles are generated on the liquid surface by the vibration energy from the ultrasonic vibrator. , The housing 255, the ultrasonic vibrator 260, and the ultrasonic transmitter 250 are provided. The ultrasonic transmitter 250 is, for example, water. Since water, which is the ultrasonic transmitter 250 held by the housing 255, has a large specific heat, the temperature of the water including the water 240 that comes into contact with the housing 255 through the housing 225 does not easily rise, and the humidifying device 210 as a whole is used for a long time. Suitable for. The mist droplet generating means 270 and the liquid container 280 are in close contact with the boundary 285 with a substance such as non-volatile oil that easily transmits ultrasonic waves sandwiched between them.

The ultrasonic vibrator 260 is controlled by a controller (not shown) included in the control device 10. The controller includes a CPU, RAM, ROM, and the like for controlling the entire humidifying device 10. The CPU is a so-called central processing unit, and various programs are executed to realize various functions. The RAM is used as a work area and a storage area of the CPU, and the ROM stores an operating system or a program executed by the CPU. The controller has a function of monitoring the deep temperature, gas temperature, gas flow rate, etc., performing feedback control (PID control, etc.) of the heater of the mist drop heating means 230, and adjusting to a predetermined temperature and humidity. Is desirable. Further, when the amount of water 240 in the liquid container 280 becomes less than the predetermined amount, it is desirable to issue a warning.

The amount of fog droplets generated by the fog droplet generating means 270 is controlled by the controller. For example, when the amplitude of the AC voltage applied to the ultrasonic vibrator 260 is increased, the amplitude of the vibration of the ultrasonic vibrator 260 is increased, and the amount of fog droplets generated is increased. It is desirable that the liquid container 280 can be removed from the housing 225. It is also desirable that the mist droplet generating means 270 be removable from the liquid container 280.

The humidifying device 210 has a flow path through which the gas to be supplied flows, and the flow path is closed by the water retention member 220, and the liquid container 280 and the mist drop generating means 270 are arranged on the blower (blower) 40 side. The water retention member 220 separates the upstream side and the downstream side, which is the user side. Specifically, the water retention member 220 is tubular and has a bottom. On the opening side of the cylinder, an end portion is joined to the inner peripheral surface of the housing 225 to block the flow path. It is desirable to increase the aeration area in order to reduce the resistance of the gas as it passes through the water retention member 220. Therefore, it is preferable to provide a spacer between the cylindrical water-retaining member 220 and the inner peripheral surface of the housing 225 to secure a gap. Instead of providing the spacer, the diameter of the cylinder of the water retention member 220 may be made sufficiently smaller than the inner diameter of the housing 225 to ensure a gap. The water-retaining member 220 is a non-woven fabric having water absorption, and it is desirable that the water-retaining member 220 is replaceable. The material of the non-woven fabric constituting the water-retaining member 220 is, for example, polypropylene, and it is desirable to perform a surfactant treatment, a fluorine gas treatment, a sulfonate treatment, an acrylic acid graft treatment, a plasma discharge treatment, or the like in order to make it hydrophilic.

The water-retaining member 220 is installed in the housing 225, and the mist-drop heating means 230 that heats the mist-drops and vaporizes them into water vapor is installed inside the water-retaining member 220, that is, on the liquid container 280 side. The mist drop heating means 230 is a resistance heating heater composed of, for example, a nichrome wire, to which a power source (not shown) is connected, and the electric power is controlled by a controller based on a gas temperature or the like to control the temperature and humidity. The water retention member 220 blocks the mist droplets, but the gas containing water vapor can pass through the water retention member 220.

Next, the operation of the humidifying device according to the above-described modified embodiment will be described with reference to FIG.

The dry gas is supplied to the humidifying device 210 from the blower (blower) side pipe 290. It is the role of the humidifying device 210 to add water to this gas, and humidification is performed by the following two methods.

(1) The mist droplets generated on the surface of the liquid container 280 are vaporized by the mist droplet heating means 230 to become water vapor. The vibration energy of the ultrasonic waves generated by the ultrasonic vibrator 260 is transmitted to the water surface of the liquid container 280, and the surface tension of a part of the water surface is weakened to generate fine mist droplets. Since the mist droplet is a minute droplet, it has a large surface area compared to its volume and is easily vaporized. Further, when the mist drop reaches the vicinity of the mist drop heating means 230, the temperature is high and the saturated vapor pressure becomes high, so that it becomes easier to vaporize. The water vapor generated by vaporization humidifies the dry gas as a result.

(2) When the mist droplets generated on the surface of the liquid container 280 reach the water retention member 220, they adhere to the water retention member 220. Since the water retention member 220 has water absorption, the water adhering to the water retention member is retained as liquid water. The water vapor pressure of the gas supplied from the blower (blower) side pipe 290 is further increased and humidified by the moisture retained in the water retention member 220 when passing in the vicinity of the water retention member 220.

The humidifying device 210 according to the modified embodiment described above can humidify by generating steam with a smaller amount of energy than the vaporization by normal boiling. Further, since a large amount of water vapor can be generated without boiling the stored water 240, the humidity can be controlled independently of the temperature without excessively raising the temperature of the gas, which is an excellent effect. Further, since the gas to be sent is filtered by the water retention member 220, the water retention member 220 has an effect of acting as a bacterial filter at the same time as humidification.

As another modification, it is conceivable to change the gas temperature based on the body surface temperature instead of changing the gas temperature based on the core body temperature. FIG. 12B is a graph showing the relationship between the time and the “relative temperature of the instep of the limbs to the body”. "Relative temperature of the instep to the body" is defined as the skin temperature of the instep of the limbs minus the skin temperature under the clavicle at the base of the neck (close to the temperature of the torso or trunk). .. Assuming that the above-mentioned "relative temperature of the instep of the limbs to the body" is represented as the body surface temperature, it can be seen that there is a correlation between the body surface temperature and sleepability by comparing FIGS. 12B and 12C. That is, when the body surface temperature rises, it becomes easier to sleep, and conversely, when the body surface temperature decreases, it becomes difficult to sleep. It is considered that this reflects that the human body releases a large amount of heat from the skin in order to lower the core body temperature, and suppresses the heat release from the skin in order to raise the core body temperature. Therefore, if the body surface temperature is measured in such an embodiment, it is possible to realize a breathing assist device capable of controlling the gas temperature based on the fluctuation of the core body temperature without preparing a special deep body temperature sensor, and breathing. It has the effect of enabling more comfortable sleep in assistance.

Specifically, in FIG. 1, the deep body temperature sensor 120 is read as a body surface temperature sensor, and in FIG. 2, the deep body temperature measuring unit 160 measures the body surface temperature, which is the temperature of the user's body surface. It is desirable to read it as a part. That is, the biological information acquisition unit 140 has a body surface temperature measuring unit that measures the body surface temperature, which is the temperature of the user's body surface, and the temperature fluctuation unit 130 has a body surface temperature measured by the body surface temperature measuring unit. The heating unit 80 is controlled so as to lower the gas temperature when the temperature rises.

Further, as another modification, it is conceivable to attach an acceleration sensor to the user to detect the body movement of the user, capture the body movement, and change the gas temperature based on the information.

During sleep, when the body movement is large, the so-called light sleep, that is, "REM sleep" state, and when the body movement is small, the so-called deep sleep, that is, "non-REM sleep" state. From the body movement information detected by the acceleration sensor to the control device 10 of the breathing assist device 1, the body movement measuring unit that measures the body movement and the body movement measured by the body movement measuring unit indicate the depth of sleep of the user. A sleep depth determination unit for determination is provided. Then, when the depth of sleep is deepened, it is conceivable that the temperature fluctuation unit 130 lowers the gas temperature.

The respiratory assist device 1 of the above-described embodiment has a remarkably excellent effect of enabling more comfortable sleep in respiratory assist.

Needless to say, the above modified examples can be applied to all the embodiments and modified examples described in the present specification.

FIG. 13 is an explanatory diagram illustrating the respiratory assist device 1 according to the fourth embodiment of the present invention. The breathing assist device 1 includes a control device 10 that controls the entire breathing assist device 1, and a main body 5 having a blower (blower) 40 that sucks gas from the intake port 30 and sends it out to the user via the breathing circuit 70. .. A flow rate measuring device 20 for measuring the flow rate of gas is provided on the outlet side of the blower (blower) 40. Further, the respiratory assist device 1 includes a humidifying device 50 that moistens the gas to be sent. By evaporating the water stored in the water storage section 55 from the porous hollow fiber section 60, the gas supplied in the breathing circuit 70 is humidified.

Specifically, the breathing assist device 1 is attached to the user to deliver the gas, the breathing interface device 110, the gas temperature measuring unit 105 that measures the gas temperature, which is the temperature of the gas, and the heating that heats the gas. A temperature fluctuating unit 130 (see FIG. 14 described later) that fluctuates the gas temperature by controlling the heating unit 80 and a heating unit 80, and a biological information acquisition unit 140 (FIG. 14 described later) that acquires biometric information of the user. (See), specifically, a brain wave measuring unit 1010 for measuring and acquiring a user's brain wave is provided, and the temperature fluctuating unit 130 controls the heating unit 80 so as to fluctuate the gas temperature based on the acquired brain wave. Do it. For example, the biological information acquisition unit 140 further includes a sleep level determination unit 1020 (see FIG. 14 described later) that determines a sleep level indicating the sleep level of the user based on the acquired biological information.

The electroencephalogram is measured by the electroencephalogram measuring unit 1010 using an electrode probe attached to the user's head, but since it is a well-known technique, detailed description thereof will be omitted.

The heating unit 80 is connected to the heater power supply 90, and the heater power supply 90 is controlled by the control device 10, so that the temperature of the gas is changed. At this time, for example, it is desirable that the control device 10 controls the temperature to be supplied to rise or fall to a predetermined temperature by feeding back the temperature measured by the gas temperature sensor 105.

As a modified embodiment, the respiratory assist device 1 determines whether the user is in an awake state or a sleeping state based on, for example, an electroencephalogram measured by the electroencephalogram measuring unit 1010. A state determination unit may be provided. Further, an electroencephalogram determination unit for determining whether the user is in REM sleep state or non-REM sleep state based on the measured electroencephalogram may be provided. Further, it is conceivable that the temperature fluctuation unit 130 controls the heating unit 80 to raise or lower the gas temperature based on whether the user is in the REM sleep state or the non-REM sleep state. Specifically, for example, when the brain wave determination unit determines that the user is in a non-rem sleep state, the temperature fluctuation unit 130 may control the heating unit 80 to lower the gas temperature.

It is also conceivable that the electroencephalogram determination unit determines the sleep depth of the user in more detail. Specifically, the brain wave determination unit determines the degree of non-rem sleep of the user, for example, the sleep stage of non-rem sleep, and the temperature fluctuation unit 130 controls the heating unit 80 based on the degree of non-rem sleep. The gas temperature may be raised or lowered.

FIG. 14 shows a configuration diagram of the control device 10 in the respiratory assist device 1 according to the fourth embodiment of the present invention. The control device 10 includes a temperature fluctuation unit 130, a biological information acquisition unit 140, and a gas temperature measurement unit 180 for measuring the temperature of the gas to be sent. The biological information acquisition unit 140 has an electroencephalogram measurement unit 1010 and a sleep level determination unit 1020 that determines a sleep level, which is the sleep level of the user, based on the electroencephalogram measured by the electroencephalogram measurement unit 1010. Specifically, the sleep level is a sleep state generally classified by the waveform of an electroencephalogram, that is, REM sleep and sleep stage 1 to sleep stage 4 (non-REM stage 1 to non-REM stage 4) of non-REM sleep. Further, the method of dividing the sleep level may be, for example, REM sleep and non-REM sleep, or may be another classification such as light sleep and deep sleep.

When the sleep level determination unit 1020 determines from the waveform of the brain wave that the user (measured person) is in the awake state, the sleep level determination unit 1020 does not determine the sleep level.

The gas temperature measuring unit 180 measures and acquires the gas temperature with, for example, a gas temperature sensor 105 (see FIG. 13). Then, the control device 10 controls the electric power output to the heater provided in the heating unit 80 by controlling the heater power supply 90 by, for example, PID control.

FIG. 15 shows an explanatory diagram of the correlation between sleep depth and core body temperature. Specifically, an example showing how the sleep depth determined based on the waveform of the brain wave and the core body temperature change with the passage of time from the awake state to the sleep onset state until the person wakes up. Is. The horizontal axis of FIG. 15 is time, the upper solid line represents the sleep depth, and the lower dashed line represents the core body temperature. Specifically, the sleep level is defined from the waveform of the user's brain wave, and is classified into REM sleep and sleep stage 1 to sleep stage 4 (non-REM stage 1 to non-REM stage 4) of non-REM sleep. In the sleep-onset region 980, the measured sleep level of the subject shifts to non-REM sleep via REM sleep, and the sleep depth is deepened from stage 1 to stage 4 of non-REM sleep. After that, it shifts to REM sleep, and then shifts to non-REM sleep again. During the sleep region 990 in which the non-REM sleep and the REM sleep are repeated several times, the core body temperature shown by the broken line decreases. Then, in the awakening region 995, which becomes awakeful after the last REM sleep, the core body temperature rises.

When the respiratory assist device 1 sends, for example, a gas having a constant temperature to the lungs in the human body, which also acts as a heat exchanger such as a radiator, such a natural change in core body temperature occurs. The quality of sleep may be impaired and the comfort of the user may be impaired. Conversely, if the temperature of the gas supplied by the respiratory assist device 1 is fluctuated so as not to interfere with the natural change in core body temperature as shown in FIG. 15, the comfort of the user can be improved.

If the sleep level is determined from the measured brain waves, a gas having a temperature that easily lowers the core body temperature, specifically, a gas having a temperature lower than the core body temperature, is supplied for a certain period of time, for example. It is also possible to improve the quality of sleep of the user by making it easier to lower the core body temperature.

FIG. 16 shows a flowchart for controlling the temperature of the insufflation gas to be changed based on the brain wave.

First, when the power of the respiratory assist device 1 is turned on, the blower (blower) 40 starts operation and starts respiratory assist (see FIG. 13). Although not shown in particular, the set value (prescription pressure, etc.) immediately before the power was turned off last time is automatically reflected when the power is turned on.

A timer function (not shown) for measuring the operation time is activated from the start of the operation, and the gas temperature is raised to a predetermined temperature, for example, 37 ° C., and maintained for a predetermined time, for example, 30 minutes (step S3-10). .. This is because it is more comfortable for the user to send a relatively warm gas when falling asleep because the passage through the nasal cavity is improved. It is desirable that the predetermined time and the predetermined temperature can be appropriately changed by the user.

When the electroencephalogram measuring unit 1010 measures the electroencephalogram waveform (step S3-20) and the sleep level determination unit 1020 determines the sleep level of the user (YES side of step S3-30), the control device 10 is the temperature fluctuation unit. The 130 controls the heater power supply 90 to lower the temperature of the heating unit 80, thereby lowering the gas temperature to a predetermined target temperature (step S3-40). This target temperature is lower than the core body temperature, preferably the same as the outside air temperature, or 1 ° C. to 3 ° C. below the outside air temperature. When the target temperature is substantially equal to the outside air temperature, the temperature fluctuation unit 130 may reduce the power given to the heater power supply 90 or set it to zero.

When the sleep level determination unit 1020 does not determine the sleep level of the user (NO side of step S3-30), specifically, when the user is in an awake state, the control device 10 determines the temperature of the gas, for example. Maintain at 37 ° C.

According to the respiratory assist device 1 according to the fourth embodiment of the present invention, the biological information acquisition unit 140 for acquiring the biological information of the user is provided, and the temperature of the gas to be supplied can be changed based on the acquired information. Therefore, it is possible to supply gas at the optimum temperature for the user, which has an excellent effect of improving the comfort of the user.

According to the breathing assist device 1 according to the fourth embodiment of the present invention, the user includes a sleep level determination unit 1020 that determines the sleep level of the user based on the biological information acquired by the biological information acquisition unit 140. The temperature of the insufflation gas can be changed to a temperature suitable for the sleep level of the user, which has an excellent effect of improving the comfort of the user.

As a modified embodiment of the present invention, the respiratory assist device 1 determines whether the user is awake or asleep based on the electroencephalogram measured by the electroencephalogram measuring unit 1010. A state determination unit may be provided. Further, it is provided with an electroencephalogram determination unit that determines sleep stages 1 to sleep stages 4 (non-REM step 1 to non-REM step 4) of REM sleep and non-REM sleep, and the control device 10 sends air by the temperature fluctuation unit 130 based on the determination. The temperature of the gas may be varied. Specifically, it is desirable to change the temperature of the gas to be supplied so as not to interfere with the natural change in core body temperature as shown in FIG.

More specifically, it is said that the subject (user) is in a sleep area 990 (see FIG. 15) that repeats non-REM sleep and REM sleep several times, provided with an electroencephalogram determination unit for determining non-REM sleep and REM sleep. When the electroencephalogram determination unit determines, it is desirable to lower the temperature of the gas to be sent so as not to hinder the decrease in the core body temperature. Alternatively, it may be maintained at a temperature lower than the minimum core body temperature, and if the temperature of the environment in which the user is sleeping is lower than the body surface temperature, the gas at the temperature of the environment in which the user is sleeping It is also possible to continue to send air.

The state determination unit and the electroencephalogram determination unit may be provided in the biological information acquisition unit 140 (see FIG. 14). Further, the state determination unit and the brain wave determination unit may be integrated with the sleep level determination unit.

Generally, when a person goes to sleep, the core body temperature of a person drops. Therefore, for example, if a gas having a temperature higher than the body surface temperature is continuously supplied, the decrease in the core body temperature is hindered, which is unpleasant for the user and may deteriorate the quality of sleep in some cases. According to the modified embodiment of the present invention, the state determination unit for determining whether the user is in the awake state or the sleeping state based on the brain wave is provided. The temperature of the gas to be anxious can be changed to a temperature suitable for sleeping, which has an excellent effect of improving the comfort of the user.

Human sleep is classified into REM sleep and non-REM sleep according to the way the brain works. In general, sleep alternates between non-REM sleep and REM sleep, from falling asleep to waking up. And there is a correlation between the repeated process and the time change of core body temperature. According to the modified embodiment of the present invention, since non-REM sleep and REM sleep can be determined from the measured brain waves, the state of core body temperature can be estimated, and the temperature of the insufflation gas is changed to a temperature suitable for the user. It has an excellent effect of getting.

It is known that the core body temperature of a person decreases with the transition from the first REM sleep to the non-REM sleep after falling asleep, and the core body temperature increases as the stage of the non-REM sleep becomes shallower. .. According to the modified embodiment of the present invention, since the change in the core body temperature can be estimated based on the brain wave, the temperature of the gas to be sent can be changed so as not to interfere with the natural fluctuation of the core body temperature, so that the user is comfortable. It has an excellent effect of improving sex.

In general, sleep alternates between non-REM sleep and REM sleep, from falling asleep to waking up. And there is a correlation between the repeated process and the time change of core body temperature. Specifically, it is known that the core body temperature tends to decrease as the sleep stage of non-rem sleep becomes deeper, and the core body temperature decreases with each non-rem sleep repeated several times until waking up. According to the modified embodiment of the present invention, when the brain wave determination unit determines that the user is in a non-rem sleep state, the temperature fluctuation unit 130 controls the heating unit 80 to lower the gas temperature. It has the excellent effect of being able to fluctuate the temperature of the gas so as not to interfere with the natural changes in core body temperature.

A person's core body temperature tends to decrease when the degree of non-rem sleep, specifically the sleep stage of non-rem sleep, becomes deeper and is maintained when the degree of non-rem sleep becomes shallower. According to the modified embodiment of the present invention, since the electroencephalogram determination unit capable of determining the degree of non-rem sleep is provided, the temperature of the gas can be changed so as not to interfere with the natural change of the core body temperature. Has an effect.

FIG. 17A shows a configuration diagram of a control device 10 that controls the respiratory assist device 1 according to the fifth embodiment of the present invention.

In the control device 10, the temperature fluctuation unit 130, the gas temperature measurement unit 180 for measuring the temperature of the gas to be sent, and the setting for changing the gas temperature according to a predetermined order and time interval are input and recorded in advance. The setting recording unit 195 is provided. Specifically, the temperature fluctuation unit 130 includes a timer processing unit 190 that controls the gas temperature with the passage of time based on the settings recorded in the setting recording unit 195. Further, it is desirable that the temperature fluctuation unit 130 feedback-controls the gas temperature measured by the gas temperature measurement unit 180.

Since the other configurations of the respiratory assist device 1 are common to the fourth embodiment of the present invention except for the electroencephalogram measuring unit 1010, the description thereof will be omitted.

FIG. 17B shows a graph showing a control result in which the air supply gas temperature is varied according to a predetermined order and time interval. The temperature of the gas to be supplied is controlled by the timer processing unit 190 included in the temperature fluctuation unit 130 according to the setting recorded in the setting recording unit 195. Specifically, the timer processing unit 190 is the temperature of the gas to be supplied for 30 minutes after the respiratory assist device 1 starts operation when the temperature of the environment in which the user is present is, for example, 23 ° C. Includes a rising region 1030 that raises to 37 ° C. Further, the timer processing unit 190 includes a maintenance region 1040 that maintains the temperature of the gas for 30 minutes after the rising region. Further, the timer processing unit 190 includes a descending region 1050 that lowers the temperature of the gas for 30 minutes after the maintenance region 1040. After that, the timer processing unit 190 controls the gas temperature so as to include the maintenance region 1060, the descending region 1070, and the maintenance region 1080.

According to the breathing assist device 1 according to the fifth embodiment of the present invention, since the temperature fluctuation unit 130 has a timer processing unit 190 that controls the gas temperature with the passage of time, the gas temperature is controlled according to a preset timer program. It can easily improve the comfort of the user.

When insufflating gas through the nasal cavity, the gas temperature slightly higher than the body surface temperature may improve the passage of the nasal cavity in the awake state. According to the respiratory assist device 1 according to the fifth embodiment of the present invention, the air supply gas is used for an average time, for example, 30 minutes, from the time when the user starts operating the device to the time when the user falls asleep. Maintaining the temperature above the body surface temperature has the excellent effect of improving the passage of the nasal cavity and making it easier for the user to fall asleep.

A person's core body temperature fluctuates over time from falling asleep to waking up. According to the respiratory assist device 1 according to the fifth embodiment of the present invention, the temperature of the gas to be sent can be changed according to a predetermined order and time interval input in advance, so that the time of the expected core body temperature can be changed. Since the air can be supplied at the optimum gas temperature according to the fluctuation, it has an excellent effect of improving the comfort of the user.

As a modified embodiment of the present invention, for example, it is conceivable that the timer processing unit 190 controls to stop the heating unit 80. Generally, the transition from wakefulness to sleep lowers a person's core body temperature. Therefore, for example, if a gas having a temperature higher than the body surface temperature is continuously supplied, the decrease in the core body temperature is hindered, which is unpleasant for the user and may deteriorate the quality of sleep in some cases. According to the above-described modification, the heating of the gas can be automatically stopped after an average time, for example, 30 minutes, which is considered to be taken from the time when the user starts operating the device to falling asleep. Therefore, the temperature of the gas can be lowered to at least room temperature so as not to interfere with the natural change in the core body temperature, which has an excellent effect of improving the comfort of the user.

Further, as a modified embodiment of the present invention, it is conceivable that the timer processing unit 190 controls the temperature of the gas to be equal to or lower than the body surface temperature of the user. Generally, the transition from wakefulness to sleep lowers a person's core body temperature. Therefore, for example, if a gas having a temperature higher than the body surface temperature is continuously supplied, the decrease in the core body temperature is hindered, which is unpleasant for the user and may deteriorate the quality of sleep in some cases. According to the above-mentioned modification, the temperature of the gas to be supplied can be automatically lowered from the body surface temperature over time, so that the temperature of the gas is at least not disturbed so as not to interfere with the natural change of the core body temperature. Since it can be lowered to room temperature, it has an excellent effect of improving the comfort of the user.

Further, as another modification of the present invention, it is conceivable that the timer processing unit 190 controls the temperature of the gas to be higher than the melting point of water in the environment in which the breathing assist device 1 is operated. .. The respiratory assist device 1 is intended for users who have few problems except for the respiratory organs, and lowering the temperature of the insufflation gas more than necessary impairs the comfort of the user. According to the modification described above, by maintaining the temperature of the insufflation gas at a temperature higher than the freezing point of water, specifically the melting point of water in the environment in which the device is operated, an unnecessarily cold gas is released. Since it is not sent air, it has an excellent effect that it does not impair the comfort of the user.

Further, as another modification of the present invention, when the gas temperature is lowered or changed to a predetermined target temperature, it is conceivable to set the target temperature in various ways based on the outside air temperature and the body surface temperature. For example, when the target temperature of the gas temperature is set based on the outside air temperature T _out (unit is Celsius temperature: ° C), which is the temperature of the place where the user is, the temperature is (T _out -10) ° C or higher and T _out . It is possible to make it less than. Alternatively, for example, when the target temperature of the gas temperature is set based on the outside air temperature T _out , it is conceivable to set the temperature to (T _out -5) ° C. or higher and lower than T _out . When the target temperature of the gas temperature is set based on the body surface temperature T _body (unit: Celsius temperature: ° C.), it is conceivable that the temperature is (T _body -10) ° C. or higher and lower than T _body . Alternatively, for example, when the target temperature of the gas temperature is determined based on the body surface temperature T _body , it is conceivable to set the temperature to (T _body −5) ° C. or higher and lower than T _body . Of course, the target temperature may be set in the same manner based on the core body temperature. For example, when the target temperature of the gas temperature is set based on the core body temperature T _deep (unit: Celsius temperature: ° C.), it is conceivable that the temperature is (T _deep -10) ° C. or higher and lower than T _deep . Alternatively, for example, when the target temperature of the gas temperature is set based on the core body temperature T _deep , it is conceivable to set the temperature to (T _deep -5) ° C. or higher and lower than T _deep . In some cases, the one with a small temperature fluctuation feels comfortable, and conversely, the one with a large temperature fluctuation feels comfortable. Therefore, it is desirable that the user can make various selections in either case.

Needless to say, the above modified examples can be applied to all the embodiments and modified examples described in the present specification.

1 Respiratory assist device 5 Main unit 10 Control device 20 Flow rate measuring device 30 Intake port 40 Blower (blower)
45 Outside temperature measurement sensor 50 Humidifying device 55 Water storage part 60 Porous hollow fiber part 65 Humidity adjusting part 70 Breathing circuit 80 Heating part 90 Heater power supply 95 Gas humidity sensor 100 User 105 Gas temperature sensor 110 Breathing interface device 120 Deep body temperature Measurement sensor 130 Temperature fluctuation unit 140 Biometric information acquisition unit 150 Humidity fluctuation unit 160 Deep body temperature measurement unit 170 Outside temperature measurement unit 180 Gas temperature measurement unit 185 Gas humidity measurement unit 190 Timer processing unit 195 Setting recording unit 210 Humidifying device 220 Water retention member 225 Housing 230 Frost heating means 240 Water 250 Ultrasonic transmitter 255 Housing 260 Ultrasonic transducer 270 Frost generating means 280 Liquid container 285 Boundary 290 Blower (blower) side piping 301 Conventional breathing assist device 301
305 Main unit 310 Control device 320 Flow rate measuring device 330 Intake port 340 Blower (blower)
350 Humidifying device 355 Water storage unit 360 Heater power supply 365 Heating unit 370 Breathing circuit 380 Heating unit 390 Heater power supply 395 Gas temperature sensor 400 User 410 Breathing interface device 1010 Brain wave measurement unit 1020 Sleep level determination unit

Claims (13)

A breathing interface device that is worn by the user and delivers gas,
A gas temperature measuring unit that measures the gas temperature, which is the temperature of the gas,
A heating unit that heats the gas,
A temperature fluctuating part that fluctuates the gas temperature by controlling the heating part, and
It is equipped with a biometric information acquisition unit that detects and acquires the biometric information of the user.
The biometric information acquisition unit further includes a sleep level determination unit that determines a sleep level indicating the sleep level of the user based on the acquired biometric information.
The temperature fluctuation unit is a respiratory assist device, which controls the heating unit so as to lower the gas temperature based on an increase in the sleep level . The respiratory assist device according to claim 1 , wherein the biological information acquisition unit includes an electroencephalogram measuring unit that measures an electroencephalogram of the user. A claim comprising a state determination unit for determining whether the user is in an awake state or a sleeping state based on the brain wave measured by the brain wave measuring unit. 2. The respiratory assist device according to 2. 2 . 3. The respiratory assist device according to 3. 4. The fourth aspect of the present invention is that, when the brain wave determination unit determines that the user is in the non-rem sleep state, the temperature fluctuation unit controls the heating unit to lower the gas temperature. Respiratory assist device as described in. The brain wave determination unit determines the degree of the non-rem sleep of the user, and the temperature fluctuation unit controls the heating unit to lower the gas temperature based on the degree of the non-rem sleep. The respiratory assist device according to any one of claims 4 to 5 , wherein the respiratory assist device is characterized. It is a respiratory assist device used for continuous positive pressure breathing therapy for users with sleep apnea syndrome.
A breathing interface device that is worn by the user and delivers gas,
A gas temperature measuring unit that measures the gas temperature, which is the temperature of the gas,
A heating unit that heats the gas,
A temperature fluctuating part that fluctuates the gas temperature by controlling the heating part, and
Equipped with
The temperature fluctuation unit further includes a timer processing unit that controls the gas temperature with the passage of time .
The timer processing unit controls the temperature of the gas to maintain a predetermined temperature for a predetermined time after the user starts operating the device, and after the lapse of the predetermined time, the timer processing unit performs the control. A breathing aid that controls to lower the temperature of the gas . The respiratory assist device according to claim 7 , wherein the timer processing unit controls so that the temperature of the gas is maintained at a temperature equal to or higher than the body surface temperature of the user for the predetermined time. .. The respiratory assist device according to claim 7 , wherein the timer processing unit stops the heating unit after the lapse of the predetermined time . Any of claims 7 to 9, wherein the timer processing unit controls the temperature of the gas to be equal to or lower than the body surface temperature of the user after the elapse of the predetermined time. The respiratory assist device according to one item . The tenth aspect of the present invention is characterized in that the timer processing unit controls the temperature of the gas to be higher than the melting point of water in the environment in which the apparatus is operated after the elapse of the predetermined time. The described breathing aid. It is a control method of a respiratory assist device that delivers gas to a sleeping user.
The gas temperature measuring step in which the breathing assist device measures the gas temperature, which is the temperature of the gas,
The heating step in which the breathing assist device heats the gas, and
The temperature fluctuation step in which the breathing assist device fluctuates the gas temperature by controlling the heating unit, and
The respiratory assist device includes a biometric information acquisition step of detecting and acquiring biometric information of the user.
The biometric information acquisition step further includes a sleep level determination step for determining a sleep level indicating the sleep level of the user based on the acquired biometric information.
The temperature fluctuation step by the breathing assist device is characterized in that the heating step is changed to control the gas temperature to be lowered based on the increase in the sleep level . Control method. It is a control method of a respiratory assist device that delivers gas to users of sleep apnea syndrome for continuous positive pressure breathing therapy .
The gas temperature measuring step in which the breathing assist device measures the gas temperature, which is the temperature of the gas,
The heating step in which the breathing assist device heats the gas, and
The respiratory assist device comprises a temperature fluctuation step that fluctuates the gas temperature by controlling a heating unit.
The temperature fluctuation step by the breathing aid device further comprises a timer processing step that modifies the heating step to control the gas temperature over time .
In the timer processing step, control is performed so that the temperature of the gas is maintained at a predetermined temperature for a predetermined time after the user starts operating the device, and after the lapse of the predetermined time, the timer processing step is performed. A method for controlling a respiratory assist device, which comprises controlling so as to lower the temperature of gas .

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